Method for augmenting, reducing, and repairing bone with thermoplastic materials (as amended)

ABSTRACT

A method for augmenting a tissue including introducing into the tissue a first thermoplastic material at a first condition; treating the first thermoplastic material to achieve a second condition that includes an at least partially crystalline skin; and introducing a second material into the tissue whereby the first thermoplastic material and the second material are contained by the at least partially crystalline skin. Also a method of fracture reduction in a tissue including exposing to gamma radiation a mass of polycaprolactone characterized by a first shape; heating the mass of irradiated polycaprolactone above its melting temperature; introducing the heated mass of polycaprolactone into the tissue annulus to deform it from the first shape; allowing the material to return to the first shape.

CROSS REFERENCE TO RELATED APPLICATION

This application is based off and claims priority to U.S. patentapplication Ser. No. 11/801,779, filed May 10, 2007, which claimspriority to U.S. Provisional Patent application No. 60/799,283, filedMay 10, 2006, the content of both applications is hereby incorporatedherein by reference in their entirety.

INCORPORATION BY REFERENCE

Each and every reference cited herein is hereby incorporated byreference as if set forth in its entirety herein.

TECHNICAL FIELD OF THE INVENTION

Generally, the present invention relates to methods and materials foraugmenting and repairing bone.

BACKGROUND OF THE FIELD OF THE INVENTION

Current standards for attaching implants such as plates to bones oftenconstitute screws in a plurality of shapes. The purpose of these screwsis to transfer the load from one bone fragment to the plate or nail andback to a secondary bone fragment.

To ensure this load transfer, the screws must have a good connection inthe bone and the plate. The connection between the plate and the screwcan be achieved with an angular stable system, which transfers the loadthrough a form-fitted connection, not through friction between the plateand screw. Recent advancements in locked plating systems have enabledthe clinician to easily achieve this angular stable construct in normalhealthy bone.

However, even angular stable constructs fail in osteoporotic bonebecause of a lack of stability in the bone to screw interface.Osteoporosis is characterized by a reduction of bone mass and also byalteration in the architecture of the bone. The trabecular bonestructure is changing significantly. These changes are taking placeafter the 6th decade of life and women are more affected than men. Thewhole skeleton is affected by osteoporosis, with varying amount ofimpact throughout the body. The regions most severely affected byosteoporosis are the spine, proximal femur, distal radius, proximalhumerus and proximal tibia. Treating osteoporotic fractures in theseareas can be very challenging for the surgeon because the screws can notfind sufficient purchase in the weak trabecular structure. There is attimes a complete absence of bone where the surgeon would normally placethe screw, such as in the proximal humerus.

One method of improving the fixation between the screw and theosteoporotic bone has been to augment the bone with a hardenablebiomaterial such as PMMA cement or calcium phosphate (CaP) cement. Eachof these methods has disadvantages.

For example, disadvantages of using PMMA include the permanentnon-resorbing nature of PMMA. It remains within the body after thefracture has healed and removal of the material is nearly impossibleonce implanted. The stiffness of PMMA is in excess of the surroundingbone creating excess stress at the interface to the bone. PMMA canrelease monomer during the curing process and the monomer can becomevascularized. PMMA releases noxious fumes during the mixing and curingprocess requiring special ventilation. PMMA is initially too runny tohandle and can quickly become too difficult to implant and the state ofthe material is not reversible. PMMA has a minimal ductility, can bindto metals making screw removal difficult, and can be difficult tocontrol the direction of implantation. PMMA can either extravasate intothe canal of the diaphysis (rendering it ineffective), into the jointspace or become vascularized (leading to an embolism). Furthermore, PMMAincludes a risk of thermal necrosis due to the exothermic reactionduring curing.

There has been recent interest in using calcium phosphate cements foraugmentation of screws and other fracture fixation devices. Calciumphosphate will slowly remodel over time and does not contain a monomer,however, it has the following deficiencies. The stiffness of calciumphosphate is in excess of the surrounding bone creating excess stress atthe interface to the bone. Calcium phosphate will inherently not perfuseinto surrounding bone without the addition of a flow enhancing agent.Calcium phosphates are subject to phase separation if they areoverpressurized. Calcium phosphate includes a variable time andtemperature dependent rheology. The calcium phosphate materials will notproperly set unless the surrounding tissue is near 37° C. It can bedifficult to control the direction of implantation of calcium phosphatesand calcium phosphates can either extravasate into the canal of thediaphysis (rendering it ineffective), into the joint space or becomevascularized (leading to an embolism). Calcium phosphates includesuboptimal mechanical properties while they often have adequatecompressive strength, they have little tensile strength, flexuralstrength or ductility. Furthermore, additional calcium phosphatematerial will not bond to calcium phosphate material that has alreadyset and the drillability and screwability of the calcium phosphate islimited.

Improvements have been made to calcium phosphate cements such as addingreinforcing fibers and flow enhancing agents. The addition ofreinforcing fibers actually renders the cement less advantageous forhardware augmentation since the fiber will be filtered by the trabecularstructure surrounding the hardware and will impede perfusion. Flowenhancing agents such as hyaluronic acid will improve some of thehandling properties of the calcium phosphate cements and will allowperfusion. However the material remains suboptimal for the application.

There also exists a need for improved materials when no fixationhardware is used. Such instances would include augmenting osteoporoticbone such as a vertebral body or to fill voids where the bone has beencompressed due to trauma. The purpose of the material in this case isnot to fixate the hardware to the bone, but rather to directly replaceor augment the bone. PMMA is commonly used for vertebroplasty proceduresbut suffers from many of the problems stated above. Calcium phosphatecements can be used as well, but also with the above limitations.Further, in these types of applications there often exists a need toreduce the fractures or to compress the surrounding bone, which theexisting materials are not capable of doing.

SUMMARY OF THE INVENTION

The present invention relates to a method for augmenting a tissueincluding the steps of introducing into the tissue a first thermoplasticmaterial at a first condition; treating the first thermoplastic materialto achieve a second condition that includes an at least partiallycrystalline skin; and introducing a second material into the tissue suchthat the first thermoplastic material and the second material arecontained by the at least partially crystalline skin.

In some embodiments, the introduction of the second material causes theat least partially crystalline skin to expand. In some embodiments, theat least partially crystalline skin is forced against at least a portionof the tissue in response to the introduction of second material intothe first thermoplastic material. This step of forcing the at leastpartially crystalline skin against at least a portion of the tissue mayinclude displacing at least a portion of the tissue. In someembodiments, at least a portion of the first thermoplastic materialsurrounds at least a portion of the second material.

In some embodiments the second material is thermoplastic material. Incertain embodiments, the first thermoplastic material and the secondmaterial are the same thermoplastic material. In some embodiments, atleast one of either the first thermoplastic material or the secondmaterial is polycaprolactone. In certain embodiments, at least one ofeither the first thermoplastic material or the second material is an atleast partially crystalline polymer. In other embodiments, the firstthermoplastic material or the second material is a substantiallycrystalline polymer. In certain embodiments, the second material isosteosynthesis hardware. In some embodiments, at least a third materialis introduced into the tissue.

In some embodiments, the tissue is bone, such as cancellous bone whichis compressed when the crystalline skin expands. In other embodiments,the tissue is mobile bone fragments, which are reduced when thecrystalline skin expands. In some embodiments, the tissue is a collapsedvertebral body, the height of which is increased when the crystallineskin expands.

In some embodiments, the step of treating the first thermoplasticmaterial includes changing the temperature of the first thermoplasticmaterial. In some embodiments, the step of treating the firstthermoplastic material includes cooling the first thermoplasticmaterial. In some embodiments, the first thermoplastic material istreated by inserting a cooling device into the first thermoplasticmaterial. In certain embodiments, the treating step includes allowingthe first thermoplastic material to achieve the second condition byexposure to ambient conditions in the tissue. In some embodiments, thesecond material is introduced when the temperature of the secondmaterial is higher than the temperature of the first thermoplasticmaterial. The second material may be introduced into the tissue in amolten state. In certain embodiments, the first thermoplastic materialand the second material are cooled after the second material isintroduced into the tissue.

In some embodiments, the first condition is a flowable state. In someembodiments, the second condition is a semi-solid state. In variousembodiments, at least a portion of the first thermoplastic material ispartially crystallized when the first thermoplastic material is at thesecond condition. In certain embodiments, at least a portion of thefirst thermoplastic material is in a semi-solid state when the firstthermoplastic material is at the second condition, and the secondmaterial is introduced into the tissue by injecting the second materialinto the first thermoplastic material. In some embodiments, thetemperature of the first thermoplastic material at the first conditionis at or above the melting point of the first thermoplastic material,and the temperature of the first thermoplastic material at the secondcondition is below the melting point of the first thermoplasticmaterial.

In some embodiments, the first thermoplastic material is injected intothe tissue. In some embodiments, the second material is injected intothe tissue. In certain embodiments, the second material is introducedinto the tissue by injecting at least a portion of the second materialinto the first thermoplastic material. In various embodiments, the firstthermoplastic material is introduced to the tissue by introducing thefirst thermoplastic material into an annulus defined by the tissue.

In various embodiments, the temperature of at least a portion of thetissue is increased prior to introducing the first thermoplasticmaterial into the tissue. In other embodiments, the temperature of atleast a portion of the tissue is decreased prior to introducing thefirst thermoplastic material into the tissue.

In certain embodiments, the first thermoplastic material and the secondmaterial are the same material and the treating step includesinterrupting the introduction of the first thermoplastic material toallow the first thermoplastic material to achieve the second conditionby exposure to ambient conditions in the tissue before the introductionof the second material. In other embodiments, the first thermoplasticmaterial is irradiated prior to introducing the first thermoplasticmaterial into the tissue. In some embodiments, the first thermoplasticmaterial is exposed to gamma radiation to induce a shape memorycharacteristic on the first thermoplastic material.

In some embodiments, the first thermoplastic material has a rate ofcrystallization that is adjusted by combining the first thermoplasticmaterial with a substance having a radiodensity that is greater than theradiodensity of the first thermoplastic material. In some embodiments,the substance includes at least one of a calcium compound, bariumsulfate, strontium carbonate, a zirconium compound, a magnesiumcompound, titanium oxides and compounds, and combinations thereof.

In some embodiments, prior to introducing the first thermoplasticmaterial into the tissue, the degree of discontinuity in the structureof the first thermoplastic material is increased to adjust the rate ofcrystallization of the first thermoplastic material. In someembodiments, increasing the degree of discontinuity in the structure ofthe first thermoplastic material includes combining the firstthermoplastic material with a radiopacifier.

In one embodiment, a method of fracture reduction in a tissue includesexposing to gamma radiation a mass of polycaprolactone characterized bya first shape; heating the mass of irradiated polycaprolactone above itsmelting temperature; introducing the heated mass of polycaprolactoneinto a tissue annulus in a shape deformed from the first shape; andallowing the mass of polycaprolactone to return to a shape thatapproaches the first shape. In some embodiments, the gamma radiationcomprises gamma radiation in the range of about 15 kGy to about 50 kGy.In one embodiment, allowing the mass of polycaprolactone to return to ashape that approaches the first shape includes cooling the mass ofpolycaprolactone. In one embodiment the cooling includes active cooling.In another embodiment, the cooling includes passive heat dissipation.

In a further embodiment, the first shape of the material includes asubstantially tubular configuration having a first diameter and whereinheating the mass of irradiated polycaprolactone above its meltingtemperature permits the introduction of the mass into an interioraperture of a cannulated device, the interior aperture having a diameterthat is smaller than the first diameter.

In some embodiments, a method for augmenting a tissue includes adjustinga rate of crystallization of a thermoplastic material by combining thethermoplastic material with a substance having a radiodensity that isgreater than the radiodensity of the thermoplastic material; introducinginto the tissue the adjusted thermoplastic material at a firstcondition; and treating the thermoplastic material to achieve a secondcondition that includes an at least partially crystalline skin. In someembodiments, the thermoplastic material at least partially includespolycaprolcatone.

BRIEF DESCRIPTION OF THE FIGURES

FIGS. 1 and 2 show PCL material injected into a drill hole of a cadaverbefore placement of a locking screw according to an embodiment of thepresent invention;

FIG. 3 shows an application of the PCL used to fill a bone void and toact as a reduction tool according to an embodiment of the presentinvention;

FIG. 4 shows a proximal femur depression filled with PCL materialaccording to an embodiment of the present invention;

FIG. 5 shows how the material of the present invention can be used toaugment the screw in the intramedullary canal according to an embodimentof the present invention;

FIGS. 6 and 7 show augmentation of a Dynamic Hip Screw (DHS) with thematerials of the present invention according to an embodiment of thepresent invention;

FIGS. 8 and 9 show a spiral nail blade modified to inject PCL materialand to allow the material to flow preferentially in one direction;

FIG. 10 is a graph showing one embodiment of a rate of recrystallizationof PCL with the addition of a radiopacifier;

FIG. 11 is a graph illustrating one embodiment of recrystallization timeof 100% PCL as a function of temperature;

FIG. 12 is a graph illustrating head displacement vs. stress cycles at1.2 kN with TFN blade in Sawbones Foam 12.5 pcf density; and

FIG. 13 is a graph showing exemplary maximum stress at bone interface.

DETAILED DESCRIPTION OF EMBODIMENTS OF THE INVENTION

The present invention is generally directed to thermoplastic materialsand methods of manipulating thermoplastic materials for theaugmentation, reduction, and repair of bone. In some embodiments, thethermoplastic materials of the present invention include crystallinealiphatic polyester polymer. In some embodiments, a preferredthermoplastic material of the present invention include polymers withhigh molecular weight (Mw), high inherent viscosity (I.V.), crystallinestructure, and low melt temperatures. In one embodiment, thethermoplastic polymer includes poly(ε-caprolactone), also known aspolycaprolactone or PCL. The preferred grade of PCL has an I.V. of about1.0 dl/g to about 1.3 dl/g and a molecular weight greater than about100,000 (Molecular weight and I.V. are generally directly correlated inpolymers). In a preferred embodiment, a PCL appropriate for the methodsand materials of the present invention is available from andmanufactured by Durect Corp. (Pelham, Ala.) and is marketed under thetrade name Lactel®. The following are the chemical and physicalproperties as provided by this manufacturer: Inherent Viscosity (dl/g)between about 1.1 dl/g to about 1.3 dl/g; Melting point, Tm (° C.)between about 58° C. and about 63° C.; Glass Transition, Tg (° C.)between about −65° C. and about −60° C.; Approximate resportion timegreater than 2 yrs; Specific Gravity about 1.11; Tensile Strength (MPa)between about 20 MPa and about 35 MPa; Elongation (%) between about 300%and about 500%; and Modulus (MPa) between about 200 MPa and about 350MPa.

Similar grades of PCL material are available from other sources such asSigma-Aldrich (St. Louis, Mo.) and others material suppliers. TheLactel® PCL polymer is manufactured under GMP conditions making itsuitable for implantation, but otherwise appears equivalent to otheravailable PCL materials of similar Mw. Although PCL is a preferredthermoplastic polymer, the use of other polymers having similar andsuitable characteristics is also contemplated for use in the invention.

PCL is a crystalline aliphatic polyester polymer. In one embodiment, theamount of crystallinity of the PCL is approximately 50%. It slowlydegrades through hydrolyzation in a manner similar to other aliphaticpolyester polymers such as polylactic acid (PLA) and polyglycolic acid(PGA). PCL's resorption time is generally longer, in the order of 2 ormore years. The desired grade of PCL is preferably a solid at ambientconditions and physiological conditions with a high degree of toughness,tensile and compressive strength. The modulus of the material isapproximately 250 MPa making it similar to the modulus of cancellousbone and an order of magnitude less stiff (lower modulus) than PMMA orcalcium phosphate (CaP) cement.

Another unique feature of PCL is that is has a melting point (Tm) ofapproximately 60° C. The crystalline structure of the material will belost above 60° C. yielding a viscous fluid that can be manipulated byhand like putty or can be injected. The material can be heated in avariety of commercially available heating devices, such as the SynthesWater Bath (available from Synthes USA, West Chester, Pa.; Part No.530.510) which heats a sterile tray of water to approximately 70° C. Thematerial can also be heated in a variety of other devices, including butnot limited to the Synthes Hot Air system, a chemical heat pack or aheated delivery gun.

In one embodiment, the PCL can be heated with a delivery gun that iscapable of holding and delivering the PCL material in an injectableform. A plunger is driven by a device similar to a caulking gun with aspring-loaded squeezable handle assembly, such as Synthes Part No.353.000. In one exemplary embodiment, a material-holding chamber similarin design to a caulking tube with an outlet or injection nozzle at oneend may be approximately 10 mm in diameter and heated by a resistiveheater that is externally powered and controlled by a standard processcontroller with a thermocouple disposed in the material chamber. In oneembodiment, the chamber is heated with a resistive material with apositive temperature coefficient (PTC) effect. In such a case theresistance of the heater will increase as the chamber nears the desiredtemperature and will maintain the appropriate temperature without theaddition of a separate temperature controller. The chamber is removeablyattached to the gun by mating pairs of flanges on the chamber and gun.Squeezing the handle advances the plunger, which in turn ejects PCL fromthe chamber nozzle. Injection temperatures of about 80° C. have beenfound to produce good results; however, other injection temperaturescapable of producing satisfactory results may also be used which is alsodependent in part on the type of polymer employed.

According to another embodiment of the present invention, an injectiondevice includes a heater powered by internal batteries with an internaltemperature controller. The batteries may be rechargeable in someembodiments. Therefore, the entire device is self-contained therebyeliminating external wires and, thus, the device can be made to bedisposable. The material chamber may be elongated or oblong in shape insome embodiments and include an injection nozzle on one end. An end ofthe chamber may be removeably attached to the Synthes gun (Part No.353.000) discussed above. The chamber may be connected to the gun viamating flanges on both the chamber and gun which may be rotatedcircumferentially into and out of engagement. The chamber may include amoveable wall which is engaged by the plunger of the gun and movedaxially to expel PCL or another thermoplastic material. In someembodiments, the chamber may be made of injection molded plasticsuitable for use in a clinical environment. The self-contained injectiondevice may include an on/off switch, adjustable or non-adjustabletemperature regulator to vary the temperature of the material and itsviscosity and working time, and various status indicators such as LED'sto indicate such parameters as “power on,” “ready” when the material hasreached the desired delivery temperature for injection, or otherparameters of interest. In some embodiments, an LCD or other display maybe provided to show the actual temperature of the device, power on,ready status, etc.

In some embodiments, the injection device may have a dual chamber. Inone embodiment, the dual chamber is contained within a single externalshell. In another embodiment, each chamber is contained within aseparate shell. In one embodiment, one chamber may contain the PCL orsimilar thermoplastic and the other chamber may contain a bioactive ortherapeutic agent such as, but not limited to, an antibiotic, growthfactor, analgesic, or other similar or dissimilar therapeutic agents.The injection device can be a two-piece or a one-piece device. In oneembodiment, the two-piece device includes a chamber and a gun. In otherembodiments, the heated chamber may be incorporated in an axialscrew-type and/or plunger device such as the syringe disclosed in U.S.Pat. No. 6,793,660, incorporated herein by reference in its entirety.

In some embodiments, the nozzle is elongated and temperature controlledto control the thermodynamic state of the material as it is beinginjected. In one embodiment the nozzle is actively cooled to reduce thetemperature of the ejected material to decrease working time, promotecrystallization and/or reduce the risk of thermal necrosis. In oneembodiment, the nozzle is actively heated to increase the working timeof the material, retard the rate of crystallization and/or to remelt thematerial if it has prematurely hardened in the nozzle. The means ofactively heating the nozzle may include, for example, but are notlimited to the means of heating the chamber. The nozzle may also bepassively temperature controlled through thermal conduction from theheating chamber.

Upon cooling, the PCL or similar material will again recrystallize andreturn to its original (i.e., prior to heating) crystalline state. Themethods of measuring crystallinity in PCL are disclosed by M. J.Jenkins, “The effect of molecular weight on the crystallization kineticsof polycaprolactone”, Polymers for Advanced Technologies, 2006;17:474-478. A surprising feature of this property that makes it distinctfrom the properties of a thermoset material (e.g., PMMA) or a hardeningceramic is that the material can be returned to the pliable, flowablephase if desired. For instance, if during implantation the materialprematurely hardens or if the surgeon is not content with the placementof the material or the hardware within it, it can be reheated andremanipulated. Any heating device could be used for this reheatingincluding the Synthes in Situ Bender/Cutter Kit (P/N 530.521) or thenozzle itself. Also, molten material can be applied to material that hasalready cooled. The molten material advantageously will reheat theinterface between the molten material and the cooled material and thematerials will bond. In one embodiment, PMMA and CaP cement do not bondat the interface and additional material cannot be added. Therefore,these latter materials do not provide the same flexibility for finetuning the implantation.

In some embodiments, the material will not recrystallize immediatelyupon cooling to a temperature below Tm. In such embodiments, thematerial remains pliable and flowable for a period of time despite thetemperature being below Tm. This allows the user to handle and work withthe material at temperature below Tm with bare hands without burning. Inone embodiment, this allows for implantation and manipulation of thematerial into a tissue without a risk of necrosis.

It has further been found in simulated injection models at bodytemperatures, that material that has been heated to 80° C. willimmediately cool to a temperature of less than about 50° C. upon contactwith the bone, yet the material remains flowable. This featureadvantageously allows for implantation without the risk of thermalnecrosis. PMMA on the other hand remains exothermic for an extendedperiod of time and can achieve temperatures in excess of about 90° C.Due to this delay of recrystallization, it is possible to utilize highermelting point materials than previously disclosed in U.S. Pat. No.6,290,982 while still retaining clinically acceptable results.

All molecular weights of PCL will generally melt at 60° C. However, theviscosity of the material above the melt point is significantlyaffected. The use of low melt polymers for injection has focused onrelatively low Mw aliphatic polyesters. For example, U.S. Pat. No.6,290,982 discloses Mw of less than 10,000 where the material hardensinto a wax, not a structural solid; U.S. Pat. No. 4,645,503 disclosespolymers in the range of 400-5000 Mw; and U.S. Pat. No. 5,679,723discloses injecting a material with an I.V. of between 0.05 and 0.5, thedisclosure of each U.S. Patent is hereby incorporated by reference inits entirety.

The PCL of the present invention can be readily blended with a varietyof materials through standard methods including melt or solventblending. In one embodiment, melt blends are made with barium sulfate,strontium carbonate and β-TCP. In one example, blending at a β-TCP topowder ratio of 70/30, 85/15, 92.5/7.5 was used. In another example,blends having a ratio of β-TCP to barium sulfate of 99/1, 99.5/0.5 wereused. In one embodiment, solvent blending was used to produce PCL/β-TCPblends at a ratio of 60/40. In one embodiment, blends are useful byallowing better visualization through X-ray during surgery. In oneembodiment, the blend with β-TCP is useful since a β-TCP blend has acomposition similar to that of bone. In one embodiment, anotherosteoconductive phase of calcium is used (e.g., hydroxyapatite).

In a preferred embodiment, a radiopacifier is combined with the PCL ofthe present invention. The radiopacifier provides several advantages,such as enabling the PCL to be visualized by a surgeon during and afterimplantation. Fluoroscopic visualization is especially important whenthe material is injected in areas without direct visualization such as,for example, a screw hole or a vertebral body, to ensure that theplacement of the material is appropriate. Examples of radiopacifiersuseful with the present invention include calcium compounds, bariumsulfate, strontium carbonate, zirconium compounds, magnesium compounds,titanium oxides and compounds, combinations thereof, and the like. Ingeneral, any element or compound with a radiodensity greater than theradiodensity of the polymer matrix could be used.

Another surprising result of combining a radiopacifier with the PCL ofthe present invention is the formation of nucleation sites within thePCL during hardening of the PCL. In one embodiment, as PCL cools andbegins to crystallize, the crystallization first takes place in theareas of discontinuity. Radiopacifiers increase the degree ofdiscontinuity in the polymer structure. In one embodiment, adding theradiopacifiers increases the number of nucleation sites which allows forfaster crystallization (e.g., setting) time. This allows for theadjustment of the working time of the polymer. FIG. 10 shows theincrease in the rate of recrystallization with the addition of aradiopacifier. The effect of faster recrystallization is evident withthe addition of as little radiopacifier as approximately 0.5% by weight.

In one embodiment, adding radiopacifiers will decrease the tensilestrength after hardening.

Other materials that can be blended with PCL include calcium materialsin the form of powders and granules. In a preferred embodiment, β-TCPsuch as the Synthes commercial product chronOS™ is combined with the PCLof the present invention. Small amounts (e.g., up to about 5% by weight)of fine β-TCP particles may be added to the PCL to provide radiopacityand enhanced osteoconductivity of the surface. In one embodiment, thefine particles have a particle size range of 1 μm to 50 μm. In oneexample, the fine particles of β-TCP used are available from Fluka.However, large amounts (e.g., about 10% by weight or greater) of β-TCPgranules in the order of between about 0.5 to about 2.8 mm diameters canalso be added to PCL at ratios of up to 80% or more by weight. In someembodiments, the blended material may no longer be readily injectable,but can still be manipulated as putty when heated above the meltingtemperature (Tm) and becomes rigid when fully recrystallized.

In some embodiments, by utilizing a high molecular weight PCL andselecting relatively large granules (e.g. about 1.4 mm to about 2.8 mm),it is possible to prevent encapsulation (e.g., PCL in the melt phasecompletely covering the β-TCP particle and thus preventing the β-TCPfrom coming into direct contact with cells) of the calcium phase. Forexample, in embodiments where an interconnectivity of the calcium phaseis maintained, the body will be able to remodel the material in vivothrough the process of creeping substitution independent of theresorption rate of the polymer. Therefore, bony ingrowth can beobtained. In one embodiment, the interconnectivity is maintained by atleast a portion of the β-TCP particles interspersed within the PCL arein contact with one another (i.e., not encapsulated). Because the β-TCPparticles are porous, an interconnected porous structure is createdthroughout the implant resulting in penetration of cells and othermaterials into the implant, leading to resorption and creation of newbone. It also provides for a degree of interconnected porosity that canbenefit the maintenance of vascularity to the surrounding bone andtissue.

Additional compounds could be added to the PCL or composite phaseincluding, but not limited to, antibiotics, growth factors, peptides,proteins, small molecules, biphosphanates, hormones, parathyroid hormone(PTH), anti-inflammatories, chemotherapeutics, antiseptics,demineralized bone, autologous bone, bone marrow aspirate, blood,platelets, platelet-rich plasma, cells, stem cells, osteoprogenitorcells, combinations thereof, and the like. These additional compoundscan be used to stimulate bone growth, maintain or increase bone mineraldensity, increase the rate of fracture healing, reduce tumor size,reduce pain or inflammation, treat infection, prevent infection,combinations thereof, and the like.

In some embodiments, thermoplastic materials (e.g., such as but notlimited to PCL) reduce encapsulation of a second composite phase. Asdiscussed above, thermoplastic materials of a preferred embodiment havean increased viscosity over existing bone augmentation materials due tothe higher molecular weight, therefore the polymer phase has less of atendency to spread out and cover adjacent composite particles. In oneembodiment, the polymer phase is more cohesive and tends to hold toitself rather than flow and spread. In one example, thermoplasticshaving a molecular weight range of 50,000 to 150,000 have an rheologicalproperties that to promote such cohesiveness.

In some embodiments, the materials of the present invention provideimproved control of the materials during injection. The prior art taughtthe benefit of using a lower Mw material for improved flow duringinjection, however, lower Mw materials provide less control of thematerial during injection than materials of higher Mw. In someembodiments, the use of high Mw material actually provides increasedcontrol over the direction of injection. The polymer will tend to flowin the direction of injection and will have less of a tendency tobackflow. This is especially advantageous when trying to apply thematerial to cancellous bone that is adjacent to an intramedullary canal,area devoid of cancellous bone such as the proximal humerus or areas ofhigh vascularity such as vertebral bodies. Low viscosity materials tendto find the path of least resistance and flow into these areaspreferentially. A higher viscosity material, such as the material of thepresent invention can flow in the direction of injection, rather thanback-flowing, and will form a bolus of material.

In some embodiments, the materials of the present invention reduceextravasation during implantation. The material according to the presentinvention has a lower tendency to extravasate and flow into joints, softtissue, vascular system, etc than the materials of the prior art. Thecohesive nature of high Mw polymers makes them prefer to adhere tothemselves, thus creating an expanding bolus of material. The prior artmaterials including PMMA, CaP cements, and lower Mw thermoplastics havemore of a tendency to creep in between fragments and into joint spacesor can become completed separated from the flow creating a particle thatcan lead to an embolitic event such as a pulmonary embolism. Such eventscan occur, for example, during vertebroplasty procedures using PMMAcement. The material of the present invention is also polymerized(unlike PMMA in its injectable state) so that the polymer chains thatprovide this improved cohesiveness are fully developed. Also, use of afully polymerized material reduces or eliminates the risk associatedwith free monomers, such as toxicity risks.

In addition to the higher Mw, the crystalline nature of the material isbeneficial for the prevention of extravasation. In one embodiment, theouter most regions of the injected bolus will have increased viscosityas it becomes crystalline and form a skin. This outer skin, while stillpliable, will not allow for significant flow. In some embodiments, theskin forms a containment barrier. Prior art bone augmentation materialsdo not have such a property. In some embodiments, the formation of skinis particularly useful to improve kyphoplasty, distal radius andproximal tibia procedures and any other procedure where theextravasation of material may have deleterious effects including butlimited to entering joint spaces, becoming vascularized or becomingentrained into bony fragments. In one embodiment, it is necessary forthe outer skin to only partially crystallize in order to form thebeneficial effects as described herein. For example, in one embodiment,when as little as about 5% to about 10% of the original crystallinity ofmaterial is achieved the material forms an outer skin that is useful forachieving the objective of the present invention including embodimentsfor preventing extravasation during the placement of thermoplasticmaterial into tissue.

Other methods of containment of injectable materials such as disclosedin US Patent Appl. Pub. No. 2005/0209629, incorporated herein in itsentirety, have required the introduction of a separate containmentdevice. In one embodiment of the present invention, a separatecontainment device is not needed to contain the injected materials. Inone embodiment, the injected material becomes its own containmentdevice.

In other embodiments, the material of the present invention providesimproved shape retention during handling and before recrystallizationover prior art bone augmentation materials. In some embodiment, the useof PCL/β-TCP putty allows for the final shape of an implant to becontrolled. For example, in one embodiment, the final shape of theimplant matches the shape of the void in the tissue.

In one embodiment, the materials of the present invention, having a highMw, have an increased viscosity before recrystallization. Therefore, thematerial holds the shape in which the material is applied or manipulatedinto. This shape may include the shape of the void created duringorthopedic trauma, a cavity that is surgically created or the desireshape for augmentation of osteosynthesis hardware. For example, wherematerial is applied in areas without adjacent support, such as a bolusof material attached to subchondral bone distally, but otherwisesurrounded by body fluids, the high molecular weight material would holdits shape where lower molecular weight material would not. One advantageto the shape-holding effect is the ability of a screw or other hardwareor fastening device to gain sufficient purchase when inserted into themolten bolus.

In some embodiments, the material of the present invention includes theability to reduce fractures and compress cancellous bone. Due to theviscous nature of the material, it can be used to move mobile bonefragments and even compress low density cancellous bone either duringinjection or if moved with digital pressure or with a bone tamp. Lowerviscosity materials will tend to flow away and will not transfer theforce.

In some embodiments, the material of the present invention includes theability to perfuse into cancellous bone and/or displace marrow. Thedisplacement of bone marrow is optimized when the viscosity of theinjected material is substantially greater than the viscosity of themarrow. The viscosity of marrow is highly variable and is temperatureand shear rate dependent. In one study, marrow has been measured at 37.5cP at body temperature. Without being limited the measurements of thisstudy, in one embodiment of the present invention, viscosity of theinjected material is substantially greater than 37.5 cP. Due to theperfusability of the material being injected in a fully polymerizedstate and due to the relatively high molecular weight and high inherentviscosity of the material, the material will tend to displace marrowwhen flowing through a cancellous structure. Another advantage to usingpolymerized material is that it will not phase separate during thisapplication. CaP cements do not inherently have this ability and willtend to phase separate if pressurized into cancellous bone with marrow.Even PMMA when initially mixed is not of sufficient viscosity todisplace marrow and will tend to channel and find paths of leastresistance. It is not until it becomes more polymerized that PMMA willdisplace the marrow rather than flow around it, however, the window oftime when working with PMMA is very limited as the material becomesfixed and is no longer movable.

Additionally, PCL has a superior cohesiveness compared to existingcements. Thus the material of the present invention rebonds to itself,even in the presence of an aqueous solution. Further, it will not bedispersed by any known bodily fluid. According to some embodiments,implanting or injecting the material of the present invention throughcancellous bone will divide the material and reincorporate the materialmany time as it passes over the trabecullae. Therefore, the ability ofthe material to rebond to itself and not disperse is of great importancewhenever a cancellous bone structure is augmented with a material suchas in vertebral body augmentation and osteosynthesis hardwareaugmentation. PMMA does not have the same level of cohesiveness in anaqueous environment and CaP cements have a tendency to become dispersein bodily fluids which affects the strength of the final set product.

In other embodiments, an especially important aspect of the presentinvention is that the properties of the injected material can bemanipulated by varying flow rates and controlling temperature within theinjected mass. In one embodiment, a hole or other access means can bedrilled into a bone such as a vertebral body, tibial plateau, distalradius, proximal femur or other metaphyseal bone region and the materialcan be injected into this space utilizing, for example, a heated injectgun as described previously. The flow of material can be stoppedtemporarily after the void is filled and the mass of material isinterdigitated into the surround bone. The polymer can be treated to atleast partially recrystallize by cooling it to below the Tm. Thistreatment can either be active cooling or passive heat dissipation. Inone embodiment, the treatment of the bolus includes simply allowing thebolus to cool. After the material has become at least partiallycrystalline, additional material can then be injected under pressure.The material that was initially injected now is at semi-solid state andis expanded by the warmer, less crystalline material of the secondinject phase. This semi-solid outer skin contains the inner, moreflowable material and a force can be generated that can be used tocompress cancellous bone, reduce mobile bone fragments, or increase theheight of a collapsed vertebral body. The entire mass of material canthen cool to physiological temperature and become fully crystalline andthe reduction is permanently maintained. In one embodiment, partiallycrystalline skin is used to reduce extravasation of the injectedmaterial by producing a containment skin as disclosed above.

In one embodiment, this procedure has an advantage over knownkyphoplasty procedures that require a specialized balloon to be inflatedfor the reduction and wherein the balloon is removed and a hardenablebiomaterial such as PMMA is then injected. In one embodiment of thepresent invention, there is the advantage of performing both operationsin one inject step which prevent loss of reduction, for example, whenthe balloon is removed. Also, extravasation of the final injectedmaterial is minimized since it is contained by the semi-solid outer skinor shell.

In some embodiments, the flow rates and temperatures of the materials ofthe present invention are adjusted to control the rate ofrecrystallization. FIG. 11 illustrates the relationship betweentemperature and the time for the material to recrystallize 10% and 50%.

As disclosed above, the materials original properties can besubstantially achieve when approximately 10% of the originalcrystallinity is developed. This time for recrystallization can beapproximately 20 minutes at 45° C. and approximately 4.5 minutes at 40°C. Thus the material can be controlled to a temperature betweenphysiological temperature and the melt temperature to yield a range ofworking times for the surgeon during the implantation period. In oneembodiment the temperature is controlled to exit the nozzle just abovephysiological temperatures or even room temperature to promote rapidrecrystallization of the material. In other embodiments, the material iscontrolled to a temperature well above physiological temperature toextend working time. The temperature of the material, in someembodiments, is controlled by varying the rate at which it is expelledfrom the system, passive heat loss as it travels through the nozzle,active cooling or heating in the nozzle, temperature in the materialholding chamber, and/or active or passive temperature control in theinjected bolus. The desired temperature range is generally betweenapproximately 37° C. and approximately 60° C. In some embodiments,temperature is controlled to a range of from approximately 0° C. toapproximately 150° C. in certain cases.

In some embodiments, the initial void or drill hole is reduced intemperature so that the initial injected material crystallizes morereadily. In another embodiment, the initial hole is heated to retardcrystallization and increase the workable time of the materials. In someembodiments, this change in temperature is generated, for example, by aheating or cooling probe or by irrigating with a solution of theappropriate temperature.

In other embodiments, the initial injected material is treated bycooling the material with an inserted probe. This would create a hollowannulus for further injection of material and cools the skin to promotecrystal formation.

In further embodiments, the injection cannula, needle, or auxiliaryinstrument is used to selectively cool and/or heat various regions ofeither the initial injection or subsequent injections of materials. Forinstance, in the case of a vertebroplasty, the anterior and posteriorportions of the injected bolus could be cooled to promotecrystallization in these regions. Thus upon further injection ofmaterial, the flow and expansion would be preferential to the radialdirection; thus allowing for a more controlled bony reduction with lessextravasation risk in undesirable areas such as towards the spinal cord.

An additional feature of one embodiment of PCL material of the presentinvention is that it has a modulus (i.e. stiffness) that is similar tohealthy cancellous bone, as illustrated below in Table 1. It also hassignificant strength in both compression and tension and excellentelongation. This combination of materials properties is unique andideally suited for the clinical application. The mechanical propertiesallow drilling and screwing of the material without cracking. The highelongation means that the material will yield with a ductile failurerather that cracking with a catastrophic failure. In some embodiments,the PCL material of the present invention has advantages over CalciumPhosphate (CaP) that is especially prone to cracking and over PMMA thatis a relatively brittle plastic and does not have the same inherentductility.

TABLE 1 Material Approximate Modulus (MPa) Cancellous Bone 250 PCL 250PMMA 3000 CaP Cement 3000

There are many benefits of matching the modulus of cancellous bone. Afilling or augmentation material that is stiffer than the surroundingbone creates a construct that is more rigid than the pre-traumacondition. It has been speculated in vertebroplasty procedures, forinstance, that this sudden and significant increase in stiffness of thevertebral body can lead to an increase in the collapse of adjacentlevels. The benefit of matching the modulus for hardware augmentationhas not been previously disclosed to the inventor's knowledge, but canbe illustrated by the following example:

As the above results illustrate, augmentation with PCL around a screwcan reduce the stress at the bone interface by 56.50%. This is expectedwith any form of augmentation since there is greater surface area. Whatis more surprising is that there is 34.07% less maximum stress whenusing PCL vs. PMMA. In this case both scenarios have the same interfacesurface area, but the lower modulus of the PCL allows the forces to betransferred over a larger area due to internal deformation of thematerial.

In one embodiment, an even lower modulus material (i.e. elastomer) mayyield even lower stress at the interface due to even more internaldeformation. However, there is a critical point where it is not failureat the bone interface, but rather the screw pulls out of theaugmentation material. In some embodiments, where screw designs havebeen optimized for performance in normal cancellous bone, matching theproperties of that bone should result in ideal screw/material interface.

According to some embodiments, potential clinical applications of thePCL material and composites include fracture fixation in the head of aproximal humerus. The proximal humerus is an especially challengingfracture in osteoporotic bone because the center resorbs and onlysubchondral bone remains. It is very difficult for screws to gainsufficient purchase in the thin shell of subchondral bone. Therefore, inone embodiment, the material of the present invention was tested as afixation method for the proximal humerus. According to one example, PCLmaterial of the present invention was injected into the cancellous boneto interdigitate with it. Screws were then placed into the semi-moltenmaterial and the construct was allowed to cool completely. The screwswere not actually in the bone, but rather the PCL was used as a bridgingmaterial between the bone and the screws. Since the PCL interdigitates,it forms a mechanical bond to the cancellous bone that exceeds thestrength of the bone. The PCL material is also drillable with standardorthopedic drills and can be redrilled when it has recrystallized. Inone embodiment, a self-drilling screw is placed directly into thematerial. Thus in one embodiment, the material is allowed to cool andthe bolus is drilled and the screw is then placed. Testing has shownthat the resistance to screw pull out is increased approximately 35% inthis embodiment vs. placing the screw in a molten bolus. Previousmaterials for hardware augmentation such as PMMA do not readily drilland leave non-resorbable debris making redrilling impractical. CaPcements are easily drilled, but often fracture during the drilling andscrewing process due to their brittle nature.

According to another embodiment, the rheological properties of the PCLmaterial can be manipulated by exposing the materials to radiation.Exposure of the material to gamma irradiation in the range ofapproximately 20 kGy to approximately 40 kGy induces a shape memoryeffect on the polymer. When the material is heated to a temperaturegreater than Tm and allowed to cool, the material will therefore have atendency to return to the shape it was when irradiated. This shapememory effect thus provides a degree of ‘spring back’ to the material.This ‘spring back’ is due to a crosslinking effect of the irradiationand has two distinct advantages. First, the spring back helps reduce orprevent extravasation of the material when the flow of the material hasceased and the most remote regions of the material will be pulledtowards the center of the bolus of the material rather than continuingto flow outward. The second advantage is that the spring back can causethe material to tighten around an implant, such as the threads of ascrew inserted into a molten mass of the material, thereby enhancing themechanical interface of the material.

In one preferred method, the PCL is exposed to gamma irradiation beforeheat melting. In one embodiment, this radiation crosslinking effect iscontrolled by the level of irradiation. In one embodiment, the source ofradiation is any high energy radiation source such as gamma irradiationor electron beam irradiation. While there is no theoretical minimum ormaximum radiation level that can be used, high levels of irradiationabove 50 kGy are known to degrade polymers and may not be practical. Inone embodiment, gamma radiation at levels of about 15 kGy to about 50kGy are used. In one embodiment, the inherent viscosity of PCL is notgreatly affected by the time that PCL is exposed to such radiation.After being placed in simulated physiological conditions, mechanicaltesting of irradiated PCL has been performed and that testingillustrates that in the first six months after such irradiation, thereis an insignificant effect on the mechanical properties of the PCL incomparison to PCL that is not irradiated. The mechanical propertiescontinue to be similar after a period of one year.

Thus, in one embodiment there is a method fracture reduction in a tissuethat includes exposing to gamma radiation a mass of polycaprolactonecharacterized by a first shape; heating the mass of irradiatedpolycaprolactone to a temperature above its melting temperature;introducing the heated mass of polycaprolactone into a tissue annulus ina shape deformed from the first shape; and allowing the material toreturn to a shape that approaches the first shape. In one embodiment,the mass of polycaprolactone is exposed to gamma radiation in acartridge that is insertable in an injection device. In one embodiment,the deformed state is achieved when the material is discharge from theinjection device (e.g., through a needle). In a further embodiment, thematerial returns to a shape that is very close the original shape (e.g.,when it cools). In one embodiment, the material is prevented fromreturning to original shape because it fills the void of a tissue beforeit reaches its original shape (e.g., when it cools). In anotherembodiment, the material substantially reaches its original shape (e.g.,when it cools).

Referring to FIGS. 1 and 2, a PCL material 102 was injected into a 4.2mm drill hole of a cadaver bone 106 before placement of a 5 mm lockingscrew 114. In some embodiments, a material 102 may include ashape-holding effect such that the material 102 supports a screw 114 orother hardware. In some embodiments, the material 102 is injected in aflowable state, such as a molten state. In some embodiments, thematerial 102 is exposed to a temperature change to achieve a secondcondition which includes an at least partially crystalline skin. Incertain embodiments, the second condition is a semi-solid state.

Referring to FIG. 3, an application of PCL material 102 was used to filla bone void 104 and to act as a reduction tool. According to someembodiments, the material 102 is heated in a water bath and applied withdigital pressure. In some embodiments, the material 102 holds a shape inwhich the material 102 is applied or manipulated into. The shape mayinclude, for example, the shape of a void 104 in a tissue. In someembodiments, gamma radiation may be used to induce a shape memorycharacteristic on a material.

Referring to FIG. 4, a proximal tibia depression was filled with PCLmaterial 102. In some embodiments, the material 102 is heated beforeinsertion. In some embodiments, the material 102 is heated in a waterbath. Upon cooling, the material 102 may be drilled to create holes 110.In some embodiments, a material 102 may be introduced into an annulusdefined by the tissue.

Referring to FIG. 5, the material 102 is shown being used to augment ascrew 112 in the intramedullary canal 118. In one embodiment, theillustrated placement of the material 102 may provide significantlyhigher pull out strength since the forces will be distributed over abroader area of the endocortex. In some embodiments, the material 102may include a shape-holding effect such that the material may support ascrew 112 or other hardware even when the material 102 is surrounded bybody fluids.

Referring to FIGS. 6 and 7, the material 102 may provide augmentation ofa DHS screw 116. In FIGS. 6 and 7, an 8 mm hole was drilled in simulatedcancellous bone 120. A bolus of material 102 was inserted into the holeand a DHS screw 116 was driven into the material 102. The PCL material102 flowed into the simulated cancellous bone 120. The material 102provided increased holding power and the ultimate failure was at the PCL102/bone 120 interface. In some embodiments, the material 102 may forman at least partially crystalline skin which may displace at least aportion of the tissue. In some embodiments, cancellous bone may becompressed when force is exerted upon it. In some embodiments, the atleast partially crystalline skin may prevent extravasation of the PCLmaterial 102.

Referring to FIGS. 8 and 9, one embodiment of the present inventionrelates to a modified nail including a channel to deliver PCL material102. A spiral blade 122 of a TFN Nail 126 (Synthes, USA) used forproximal femur fractures has been modified by removing material at themost distal end 124. The nail 126 may be inserted into a proximal femuraccording to the standard procedure. A heated cartridge of PCL may beattached to the proximal end of the blade 122 and the material 102 maybe injected under pressure to allow the material 102 to flow down thecannulation 128 and out of the most distal end 124. The modification tothe distal end 124 allows the material 102 to flow preferentially in onedirection, in this case the superior direction.

In one embodiment, the material is allowed to cool or is actively cooledafter it flows from cannulation 128. In one embodiment, the material isallowed to return at least partially to an original shape after it isallowed to cool. In one embodiment, the original shape is asubstantially tubular shape. In one example, the material has anoriginal shape that corresponds to the shape and diameter of a moldcavity in which the material was exposed to gamma radiation to induce ashape memory effect.

Cyclic compression testing was done on the construct and compared to thesame conditions without the use of PCL 102. FIG. 12 shows a graph ofhead displacement vs. stress cycles of a TFN nail in Sawbones Foam 12.5pcf density with or without PCL at a load of 1.2 kN. As FIG. 12illustrates, there is significantly less head displacement even overcyclic loading over 500,000 cycles at a load of 1.2 kN.

In order that the invention may be understood, preferred embodimentswhich are given by way of example only, are described with reference tothe appended drawings. Accordingly, the preferred embodiments aredescribed for convenience of reference and without limitation of theinvention to embodiments described. The scope of the invention beingdefined by the claims appended hereto.

EXAMPLES Example 1 PCL Composite Composition

A PCL/β-TCP composite was produced with the following composition:

PCL component: Sigma PCL 440744, I.V. 1.59, 20% by weight

β-TCP component: chronOS granules, 1.4-2.8 mm

The above components were heated to above 60° C. and kneaded by hand andallowed to cool. A structurally sound, cohesive mass was formed. Thecomposite was reheated and manipulated to simulate manipulation by thesurgeon and formed into a ball. It was again allowed to cool.

The composite material was placed in a solution with Alizarin red S (ared dye selective for calcium). Areas that still had exposed calciumwere dyed red and areas encapsulated by polymer were yellow. Asignificant amount of calcium was free from encapsulation. The samecomposite was sectioned and the dye had penetrated significant portionsof the internal structure demonstrating an interconnected porosity.

Example 2

PCL material was injected into a 4.2 mm drill hole in a cadaver and a 5mm locking screw was placed therein. The material was injected throughan injection device as described above and was used for injection set at80° C. Good perfusion into the relatively dense cancellous bone can beseen in FIGS. 1 and 2.

Example 3

A finite element analysis (FEA) was performed on a construct simulatinga stainless steel screw in cancellous bone with an offset load. Themodulus of each of the materials was assigned as reported in Table 1,above. Three conditions were tested in the FEA simulation:

1) Ø8 mm stainless steel screw in cancellous bone block withoutaugmentation

2) 3 mm of PMMA augmentation around screw

3) 3 mm of PCL augmentation around screw

The screw was rigidly constrained on the proximal end and a unit loadwas placed on the cancellous bone at the distal end. The maximum stressat the screw to bone interface was assessed with the results shown inFIG. 13.

While the detailed description represents preferred embodiments of thepresent invention, it will be understood that various additions,modifications and substitutions may be made therein without departingfrom the spirit and scope of the present invention as defined in theaccompanying claims. In particular, it will be clear to those skilled inthe art that the present invention may be embodied in other specificforms, structures, arrangements, proportions, sizes, and with otherelements, materials, and components, without departing from the spiritor essential characteristics thereof. One skilled in the art willappreciate that the invention may be used with many modifications ofstructure, arrangement, proportions, sizes, materials, and componentsused in the practice of the invention, which are particularly adapted tospecific needs and operating requirements, without departing from theprinciples of the present invention. The presently disclosed embodimentsare therefore to be considered in all respects as illustrative and notrestrictive, the scope of the invention being defined by the appendedclaims, and not limited to the foregoing description or embodiments.

1-48. (canceled)
 49. A method of preparing a modified polycaprolactonecomposition for hardware fixation as part of fracture treatment,comprising: blending a polycaprolactone composition with aradiopacifier; shaping the polycaprolactone-radiopacifier compositioninto a first shape; and inducing a shape memory property to thepolycaprolactone-radiopacifier composition; wherein a modifiedpolycaprolactone composition is formed; wherein upon heating above amelting temperature of the modified composition the modified compositionis capable of achieving a second shape deformed from the first shape;wherein upon cooling below the melting temperature of the modifiedcomposition, the modified composition has a recrystallization ratehigher than the polycaprolactone composition; and wherein upon coolingbelow the melting temperature of the modified composition, the modifiedcomposition is capable of achieving a shape that approximates the firstshape.
 50. The modified polycaprolactone composition prepared accordingto claim
 49. 51. The modified polycaprolactone composition of claim 50,further comprising at least one selected from a group consisting ofantibiotics, growth factors, peptides, proteins, small molecules,biphosphanates, hormones, parathyroid hormone (PTH),anti-inflammatories, chemotherapeutics, antiseptics, demineralized bone,autologous bone, bone marrow aspirate, blood, platelets, platelet-richplasma, cells, stem cells, osteoprogenitor cells, and combinationsthereof.
 52. The modified polycaprolactone composition of claim 50,wherein the radiopacifier is selected from a group consisting of calciumcompounds, barium sulfate, strontium carbonate, zirconium compounds,magnesium compounds, titanium oxides and compounds, and blends andmixtures thereof.
 53. The modified polycaprolactone composition of claim50, wherein the polycaprolactone composition has an inherent viscosityin the range of about 1.0 dl/g to about 1.3 dl/g
 54. The method of claim49, wherein the step of inducing a shape memory property is irradiatingthe polycaprolactone-radiopacifier composition.
 55. The method of claim54, wherein the step of irradiating uses gamma radiation in the range ofabout 15 kGy to about 501 Gy.
 56. The method of claim 49, wherein thepolycaprolactone-radiopacifier composition is shaped into asubstantially rod shape as a first shape.
 57. A method of hardwarefixation for the treatment of a bone fracture, comprising: heating amodified polycaprolactone composition having a first shape to above itsmelting point to achieve a second shape deformed from the first shape,wherein the modified composition is a polycaprolactone mixed with aradiopacifier and wherein the modified composition has an induced shapememory property; injecting the modified composition in its second shapethrough a cannulated device into a bone site; applying a fixation deviceto the bone site such that the fixation device contacts the modifiedcomposition in its second shape; cooling the modified composition belowits melting point such that the composition recrystallizes andtransitions from the second shape to a shape that approximates the firstshape, wherein the recrystallized modified composition supports thefixation device.
 58. The method according to 57, wherein the step ofapplying the fixation device occurs before the step of injecting themodified composition.
 59. The method according to 58, wherein thecannulated device is the fixation device.
 60. The method according to57, wherein the step of applying the fixation device occurs after thestep of injecting the modified composition.
 61. The method of claim 57,further comprising actively altering the temperature of the modifiedcomposition in the second state.
 62. The method of claim 61, wherein thestep of actively altering is actively heating.
 63. The method of claim61, wherein the step of actively altering is actively cooling.
 64. Asystem for hardware fixation for a bone comprising: a cannulated device;a modified polycaprolactone composition having a first shape, whereinthe modified composition is a polycaprolactone mixed with aradiopacifier and wherein the modified composition has an induced shapememory property; and an injection device injecting the modifiedcomposition in a second shape through the cannulated device into a bonesite, wherein the second shape is deformed from the first shape; and afixation device applied to the bone site such that the fixation devicecontacts the modified composition in its second shape.
 65. The systemaccording to 64, wherein the cannulated device is the fixation device.66. The system according to 64, wherein the modified polycaprolactonecomposition is shaped into a substantially rod shape as a first shape.